Image processing of images that include marker images

ABSTRACT

An image processing method, includes: obtaining an image, the image having marker images and a background image; identifying presence of an object in the background image using a processor; and providing a signal for stopping a procedure if the presence of the object is identified. An image processing apparatus, includes: a processor configured for: obtaining an image, the image having marker images and a background image; identifying presence of an object in the background image; and providing a signal for stopping a procedure if the presence of the object is identified. A computer product having a non-transitory medium storing a set of instructions, an execution of which causes an image processing method to be performed, the method includes: obtaining an image, the image having marker images and a background image; identifying presence of an object in the background image; and providing a signal for stopping a procedure if the presence of the object is identified.

RELATED APPLICATION DATA

This application claims priority to and the benefit of U.S. ProvisionalPatent Application No. 61/798,546, filed on Mar. 15, 2013, pending, theentire disclosure of which is expressly incorporated by referenceherein.

FIELD

An embodiment described herein relates to image processing, and morespecifically, to method and system for processing images that includemarker images.

BACKGROUND

Radiation therapy involves medical procedures that selectively exposecertain areas of a human body, such as cancerous tumors, to high dosesof radiation. The intent of the radiation therapy is to irradiate thetargeted biological tissue such that the harmful tissue is destroyed. Incertain types of radiotherapy, the irradiation volume can be restrictedto the size and shape of the tumor or targeted tissue region to avoidinflicting unnecessary radiation damage to healthy tissue. For example,conformal therapy is a radiotherapy technique that is often employed tooptimize dose distribution by conforming the treatment volume moreclosely to the targeted tumor.

Normal physiological movement represents a limitation in the clinicalplanning and delivery of conventional radiotherapy and conformaltherapy. Normal physiological movement, such as respiration or heartmovement, can cause a positional movement of the tumor or tissue regionundergoing irradiation. If the radiation beam has been shaped to conformthe treatment volume to the exact dimensions of a tumor, then movementof that tumor during treatment could result in the radiation beam notbeing sufficiently sized or shaped to fully cover the targeted tumoraltissue.

To address this problem, physiological gating of the radiation beamduring treatment may be performed, with the gating signal synchronizedto the movement of the patient's body. In this approach, instruments areutilized to measure the physiological state of the patient withreference to the particular physiological movement being examined. Forexample, respiration has been shown to cause movements in the positionof a lung tumor in a patient's body. If radiotherapy is being applied tothe lung tumor, then a position sensor can be attached to the patient tomeasure the patient's respiration cycle. The radiation beam can be gatedbased upon certain threshold points within the measured respiratorycycle, such that the radiation beam is disengaged during periods in therespiration cycle that correspond to excessive movement of the lungtumor.

One type of position sensor that may be used in medical gating is acamera system that includes a camera configured to sense markers on amarker block that is attached to the patient. During use, the camera isconfigured to determine the position of the marker block (whichcorresponds with the patient's physiological motion, such as breathing)based on marker images captured by the camera. In some cases, it may bedesirable to ensure that only the marker images (i.e., not images ofother objects) be used to determine the position of the marker block.Otherwise, the resulting position determined may not be the correctposition of the marker block.

As such, Applicant of the subject application believes that a new methodand system for processing images captured by a marker system camera maybe desirable.

SUMMARY

An image processing method, includes: obtaining an image, the imagehaving marker images and a background image; identifying presence of anobject in the background image using a processor; and providing a signalfor stopping a procedure if the presence of the object is identified.

Optionally, the act of identifying the presence of the object in thebackground comprises: dividing the image into a plurality of imageportions arranged in a matrix; and determines a mean or median value ofpixel values in each of the image portions.

Optionally, the act of identifying the presence of the object in thebackground further comprises determining a histogram using thedetermined mean or median values.

Optionally, the act of identifying the presence of the object furthercomprises determining if any of the mean or median values exceeds a peakvalue of the histogram by more than a specified threshold.

Optionally, the method further includes setting a size for one or moreof the image portions.

Optionally, the size is set manually.

Optionally, the size is set automatically using the processor.

Optionally, the method further includes flattening the image ingreyscale so that gradient variation across the image is reduced.

Optionally, the act of flattening the image in greyscale comprises:sampling a set of points in the image; generating an uniform gradientimage with uniform grayscale gradient which is the best-fit to thesampled set of points; and subtracting the uniform gradient image fromthe received image to generate an output image.

Optionally, the method further includes excluding the object as amarker.

Optionally, the act of receiving an image comprises receiving a sequenceof images that includes the image, and the act of identifying thepresence of the object is performed on a subset of the sequence ofimages.

An image processing apparatus, includes: a processor configured for:obtaining an image, the image having marker images and a backgroundimage; identifying presence of an object in the background image; andproviding a signal for stopping a procedure if the presence of theobject is identified.

Optionally, the processor is configured for: dividing the image into aplurality of image portions arranged in a matrix; and determines a meanor median value of pixel values in each of the image portions.

Optionally, the processor is configured for determining a histogramusing the determined mean or median values.

Optionally, the processor is configured for determining if any of themean or median values exceeds a peak value of the histogram by more thana specified threshold.

Optionally, the processor is configured to obtain a size for one or moreof the image portions.

Optionally, the processor is configured to obtain the size by receivingan input from a user that represents the size.

Optionally, the processor is configured to obtain the size bydetermining the size using an algorithm.

Optionally, the processor is further configured for flattening the imagein greyscale so that gradient variation across the image is reduced.

Optionally, the processor is configured to perform the act of flatteningthe image in greyscale by: sampling a set of points in the image;generating an uniform gradient image with uniform grayscale gradientwhich is the best-fit to the sampled set of points; and subtracting theuniform gradient image from the received image to generate an outputimage.

Optionally, the processor is further configured to exclude the object asa marker.

Optionally, the processor is configured to receive a sequence of imagesthat includes the image, and the processor is configured to perform theact of identifying the presence of the object on a subset of thesequence of images.

A computer product having a non-transitory medium storing a set ofinstructions, an execution of which causes an image processing method tobe performed, the method includes: obtaining an image, the image havingmarker images and a background image; identifying presence of an objectin the background image; and providing a signal for stopping a procedureif the presence of the object is identified.

Other and further aspects and features will be evident from reading thefollowing detailed description.

BRIEF DESCRIPTION OF THE DRAWINGS

The drawings illustrate the design and utility of various featuresdescribed herein, in which similar elements are referred to by commonreference numerals. These drawings are not necessarily drawn to scale.In order to better appreciate how the above-recited and other advantagesand objects are obtained, a more particular description will berendered, which are illustrated in the accompanying drawings. Thesedrawings depict only exemplary features and are not therefore to beconsidered limiting in the scope of the claims.

FIG. 1 illustrates a radiation system being used with a marker system.

FIG. 2 illustrates a marker system.

FIG. 3 illustrates a marker block.

FIG. 4 illustrates another marker block.

FIG. 5 illustrates a method of processing images.

FIG. 6 illustrates a technique of dividing an image into image portions.

FIG. 7 illustrates a technique of flattening an image in grayscale.

FIG. 8 illustrates an amplitude diagram and a corresponding phasediagram.

FIG. 9 illustrates a computer system.

DETAILED DESCRIPTION

Various features are described hereinafter with reference to thefigures. It should be noted that the figures are not drawn to scale andthat the elements of similar structures or functions are represented bylike reference numerals throughout the figures. It should be noted thatthe figures are only intended to facilitate the description of thefeatures. They are not intended as an exhaustive description of theclaimed invention or as a limitation on the scope of the claimedinvention. In addition, an illustrated feature needs not have all theaspects or advantages shown. An aspect or an advantage described inconjunction with a particular feature is not necessarily limited to thatfeature and can be practiced in any other features even if not soillustrated.

Radiation System

FIG. 1 illustrates a radiation system 10. The system 10 includes agantry 12 having an opening (or bore) 13, a patient support 14 forsupporting a patient 16, and a control system 18 for controlling anoperation of the gantry 12. In the illustrated embodiments, the gantry12 has a slip-ring configuration (donut shape). Alternatively, thegantry 12 can have other configurations, such as a C-arm configuration.The system 10 also includes a radiation source (e.g., x-ray source) 20that projects a beam of radiation towards the patient 16, and acollimator 21 for changing a shape of the beam. The system 10 alsoincludes a detector 24 on an opposite side of the gantry 12, which insome cases, may be used to receive radiation exiting from the patient16, and generate image(s) using the received radiation. The detector 24has a plurality of sensor elements configured for sensing a x-ray thatpasses through the patient 16. Each sensor element generates anelectrical signal representative of an intensity of the x-ray beam as itpasses through the patient 16. In other embodiments, the system 10 doesnot include the detector 24.

In the illustrated embodiments, the radiation source 20 is a treatmentradiation source for providing treatment energy. In other embodiments,the radiation source 20 may be a diagnostic radiation source forproviding diagnostic energy (e.g., energy that is suitable forgenerating an image). In further embodiments, the radiation source 20can be configured to selectively provide treatment energy and diagnosticenergy. In some embodiments, the treatment energy is generally thoseenergies of 160 kilo-electron-volts (keV) or greater, and more typically1 mega-electron-volts (MeV) or greater, and diagnostic energy isgenerally those energies below the high energy range, and more typicallybelow 160 keV. In other embodiments, the treatment energy and thediagnostic energy can have other energy levels, and refer to energiesthat are used for treatment and diagnostic purposes, respectively. Insome embodiments, the radiation source 20 is able to generate X-rayradiation at a plurality of photon energy levels within a range anywherebetween approximately 10 keV and approximately 20 MeV.

The control system 18 includes a processor 54, such as a computerprocessor, coupled to a source rotation control 40. The control system18 may also include a monitor 56 for displaying data and an input device58, such as a keyboard or a mouse, for inputting data. During a scan toacquire x-ray projection data (e.g., cone beam CT image data), thesource 20 rotates about the patient 16. The rotation of the source 20and the operation of the radiation source 20 are controlled by thesource rotation control 40, which provides power and timing signals tothe radiation source 20 and controls a rotational speed and position ofthe source 20 based on signals received from the processor 54. Althoughthe control 40 is shown as a separate component from the gantry 12 andthe processor 54, in alternative embodiments, the control 40 can be apart of the gantry 12 or the processor 54.

In some embodiments, the system 10 may be a treatment system configuredto deliver treatment radiation beam towards the patient 16 at differentgantry angles. During a treatment procedure, the source 20 rotatesaround the patient 16 and delivers treatment radiation beam fromdifferent gantry angles towards the patient 16. While the source 20 isat different gantry angles, the collimator 21 is operated to change theshape of the beam to correspond with a shape of the target tissuestructure. For example, the collimator 21 may be operated so that theshape of the beam is similar to a cross sectional shape of the targettissue structure. In another example, the collimator 21 may be operatedso that different portions of the target tissue structure receivedifferent amount of radiation (as in an IMRT procedure).

In other embodiments, the system 10 may be an imaging system. In suchcases, the collimator 21 may not be needed. During a radiation imagingprocedure, the radiation source 20 generates and directs an x-ray beamtowards the patient 16, while the detector 24 measures the x-rayabsorption at a plurality of transmission paths defined by the x-raybeam during the process. The detector 24 produces a voltage proportionalto the intensity of incident x-rays, and the voltage is read anddigitized for subsequent processing in a computer. After image data atdifferent gantry angles have been collected, the collected data areprocessed for reconstruction of a matrix (CT image), which constitutes adepiction of a density function of the bodily section being examined. Byconsidering one or more of such sections, a skilled diagnostician canoften diagnose various bodily ailments. In some cases, the one or moresections can also be used to perform treatment planning.

As shown in the figure, the radiation system 10 is used with a markersystem 200 that includes a marker block 202 and a camera 204. The camera204 is coupled to the processor 54, which in accordance with someembodiments, may be a part of the marker system 200. Alternatively,instead of the processor 54, the camera 204 may be coupled to anotherprocessor (not shown). Also, in other embodiments, the marker system 200may not include the camera 204. During use, the marker block 202 iscoupled to the patient 16 (e.g., placed on the patient's chest, abdomen,or another body part), and the camera 204 is used to view the markerblock 202. The camera 204 transmits image data to the processor 54,which processes the image data to determine a position and/ororientation of the marker block 202.

As shown in the figure, four lasers 60 a-60 d are positioned adjacent tothe system 10. The lasers 60 a-60 d are configured to generaterespective laser beams 62 a-62 d, which may be used to align the markerblock 202 (and therefore, the patient 16) at a desired location. In theillustrated embodiments, lasers 60 a, 60 b are configured to generateand project laser beams 62 a, 62 b from opposite sides of the markerblock 202, laser 60 c is configured to generate and project laser beam62 c from above the marker block 202, and laser 60 d is configured togenerate and project laser beam 62 d downwardly at an angle onto themarker block 202. In other embodiments, the lasers 60 may be configuredto project the laser beams 62 from other directions. Each laser 60 maybe mounted to any structure, such as a wall, a ceiling, a patientsupport, or another device. Although four lasers 60 are shown, in otherembodiments, more or less than four lasers 60 may be used. For example,in other embodiments, only lasers 60 a-60 c are used.

Marker System

FIG. 2 illustrates the marker system 200 of FIG. 1 in accordance withsome embodiments. The marker system 200 includes the marker block 202,the camera 204, and a processing unit 206.

The marker block 202 includes a plurality of markers 208. Each marker208 is configured to emit or reflect light. For example, in someembodiments, each marker 208 may include a LED for emitting light. Insome embodiments, each LED is configured to emit infrared light. Inother embodiments, each LED is configured to emit UV light. In somecases, each LED is configured to emit light having at least a wavelengthof 890 nm. In other embodiments, each LED is configured to emit visiblelight. Also, in some embodiments, each LED is configured to emit lighthaving a wavelength that is anywhere from 500 nm to 700 nm. In someembodiments, each LED has a half angle that is anywhere between 50° and70°, and more preferably, anywhere between 55° and 65°, such as 60°.Each LED may be configured to emit light continuously, or in pulses. Inother embodiments, instead of LEDs, the light sources may be other typesof light bulbs, such as halogen light bulbs, CFL bulbs, incandescentbulbs, etc. Also, in other embodiments, two or more of the markers 208may share a LED. For example, in other embodiments, a LED may beoptically coupled to two or more markers 208 via fiber optics. The LEDmay be located in the marker block 202, or outside the marker block 202(remote from the marker block).

In other embodiments, instead of having a light source for emittinglight, each marker 208 may include a reflective structure for reflectinglight. In such cases, the camera 204 may include a light source fordirecting light towards the markers 208, so that light can be reflectedfrom the markers 208 for detection by the camera 204.

In further embodiments, each marker 208 may include a material thatemits light in certain wavelength(s) in response to light in otherwavelength(s) received by the marker 208.

In still further embodiments, each marker 208 may be a device that doesnot emit or reflect light. For example, in other embodiments, eachmarker 208 may be any fiducial device that is coupled to the patient.

In other embodiments, instead of the shape shown in the above example,the marker block 202 can have different shapes. FIG. 3 depicts anembodiment of a marker block 202 having a cylindrical shape withmultiple reference locations comprised of markers 208 located on itssurface. FIG. 4 depicts an alternate marker block 202 having ahemispherical shape comprised of a plurality of markers 208 attached toits surface.

In other embodiments, the marker block 202 can be formed with shapes tofit particular body parts. For example, molds or casts that match tospecific locations on the body can be employed as marker blocks 202.Marker blocks 202 shaped to fit certain areas of the body facilitate therepeatable placement of the marker blocks 202 at particular locations onthe patient. Alternatively, the marker blocks 202 can be formed to fitcertain fixtures that are attached to a patient's body. For example, amarker block 202 can be formed within indentations and grooves thatallow it to be attached to eyeglasses, to a patient's clothing, or to apatient's skin. In yet another embodiment, the fixtures are formed withintegral marker block(s) 202 having markers 208 on them.

In further embodiments, the markers 208 may not be secured to a block.For example, in other embodiments, the markers 208 may be individuallysecured to, or placed on, the portions of the patient 16. In someembodiments, each marker 208 may include a LED or a reflective structuresecured to a base, wherein the base has an adhesive for attachment tothe patient 16 or to a patient's clothing. In some cases, the adhesivemay be made from a biocompatible material to reduce a risk of a skinirritation.

The camera 204 is configured for detecting the markers 208. In someembodiments, the camera 204 may include a filter system 209 thatincludes one or more filters for reducing ambient light. For example, insome embodiments, the camera 204 may include one or a combination of anotch filter, a high pass filter, a low pass filter, and a bandpassfilter. In some cases, the filter(s) is configured to reduce ambientlight while allowing at least some of the light from the markers 208 totransmit therethrough. For example, in some embodiments, the camera 204includes one or more filters for reducing ambient light to a level thatcorresponds with a noise level of the camera 204 while allowing lightfrom the markers 208 to be imaged by the camera 204. Also, in somecases, the filter(s) may be configured to reduce light being imaged bythe camera to a bandwidth anywhere within a range of 10 nm to 100 nm. Infurther embodiments, the camera 204 may include one or more neutraldensity filters for reducing ambient light intensity. In still furtherembodiments, the camera 204 may include one or a combination of abandpass filter, high pass filter, low pass filter, and neutral densityfilter. In other embodiments, the camera 204 may not include the filtersystem 209. For example, in other embodiments, the camera 204 may notinclude any notch filter, high pass filter, low pass filter, bandpassfilter, and/or neutral density filter.

In some embodiments, the camera 204 may be a charge-couple device(“CCD”) camera having one or more photoelectric cathodes and one or moreCCD devices. A CCD device is a semiconductor device that can storecharge in local areas, and upon appropriate control signals, transfersthat charge to a readout point. When light photons from the scene to beimages are focused on the photoelectric cathodes, electrons areliberated in proportion to light intensity received at the camera. Theelectrons are captured in charge buckets located within the CCD device.The distribution of captured electrons in the charge buckets representsthe image received at the camera. The CCD transfers these electrons toan analog-to-digital converter. The output of the analog-to-digitalconverter is sent to processing unit 206 to process the video image andto calculate the positions of the markers 208. In other embodiments, thecamera 204 may be other types of imaging device. For example, in otherembodiments, the camera 204 may be a CMOS camera.

As shown in FIG. 2, the processing unit 206 is communicatively coupledto the camera 204. In some embodiments, the processing unit 206 may bethe processor 54 of FIG. 1. In other embodiments, the processing unit206 may be a component of the processor 54 of FIG. 1, or anothercomponent that is communicatively coupled to the processor 54 of FIG. 1.The processing unit 206 may include hardware, software, or combinationof both. Also, in some embodiments, the processing unit 206 may includea non-transitory medium for storing data. By means of non-limitingexamples, the data may be image data captured by the camera 204,processed image data, and meta data of the image data. The processingunit 206 may be communicatively coupled to the camera 204 via a cable.In other embodiments, the processing unit 206 may be communicativelycoupled to the camera via a wireless network.

In operation, the marker block 202 is coupled to the patient 16. Themarker block 202 may be placed on the patient 16, and/or may be securedto the patient 16 may a securing mechanism (e.g., adhesive, strap, clip,etc.). The camera 204, which is directed at patient 16, captures anddetects the markers 208. The filter system 209 at the camera 204 filtersout at least some of the ambient light while allowing light from themarkers 208 to be captured by the camera 204. For example, the filtersystem 209 may reduce ambient light to a level that corresponds with anoise level of the camera 204 while allowing light from the markers 208to be imaged by the camera 204.

The camera 204 generates video images that show the position of themarkers 208 within its video frame. The video images contain mainlyimages of the LEDs and nothing else (or almost nothing else) in thefield of view of the camera 204. The generated video images are sent toprocessing unit 206 (or another processor) for further processing.

The processing unit 206 (or another processor) receives video imagesfrom the camera 204. The processing unit 206 first processes each videoimage from the camera 204 to identify images of the markers 208 in theimage frame. Based on the determined position of the markers 208, andthe known relative positions among the markers 208, the processing unit206 then determines the position (X, Y, Z) and/or orientation (θ_(x),θ_(y), θ_(z)) of the marker block 202. In some embodiments, informationregarding the location and orientation of the camera 204 is provided tothe processing unit 206 to facilitate the computations of the positionand/or orientation of the marker block 202.

A possible inefficiency in tracking the markers 208 is that the markers208 may appear anywhere on the video frame, and all of the imageelements of the video frame may have to be examined to determine thelocation of the markers 208. Thus, in an embodiment, the initialdetermination of locations for the markers 208 involves an examinationof all of the image elements in the video frame. If the video framecomprise 640 by 480 image elements, then all 307200 (640*480) imageelements are initially examined to find the location of the markers 208.

For real-time tracking of the markers 208, examining every image elementfor every video frame to determine the location of the markers 208 inreal-time could consume a significant amount of system resources. Thus,in an embodiment, the real-time tracking of the markers 208 can befacilitated by processing a small region of the video frame, referred toherein as “tracking gate”, that is placed based on estimation of thelocations of the already-identified markers 208 in the video frame. Thepreviously determined location of a marker 208 is used to define aninitial search range (i.e., the tracking gate) for that same marker inreal-time. The tracking gate is a relatively small portion of the videoframe that is centered at the previous location of the marker 208. Thetracking gate is expanded only if it does not contain the new locationof the marker 208. As an example, consider the situation when thepreviously determined location of a particular marker is image element(50,50) in a video frame. If the tracking gate is limited to a 50 by 50area of the video frame, then the tracking gate for this example wouldcomprise the image elements bound within the area defined by thecoordinates (25,50), (75,50), (50,25), and (50,75). The other portionsof the video frame are searched only if the marker 208 is not foundwithin this tracking gate.

In some embodiments, an image processing may be performed to ensure thatonly marker images are being used to determine the position of themarker block 202 or the position or state of the patient. FIG. 5illustrates an image processing method 500 that may be performed by theprocessing unit 206, or by another processing unit. First, an image isobtained (item 502). In the illustrated embodiments, the image isgenerated by the camera 204, and is transmitted to the processing unit206. Thus, item 502 may be performed by the processing unit 206receiving the image from the camera 204 in some embodiments. The imagereceived by the processing unit 206 has marker images and a backgroundimage (e.g., image of everything else that is not a marker). In otherembodiments, the image may be obtained by using the camera 204 togenerate the image.

Next, presence of an object in the background image is identified (item504). In some embodiments, item 504 may be performed using theprocessing unit 206. Various techniques may be employed in differentembodiments to detect an object in the background image that is not amarker. In some embodiments, the processing unit 206 may be configuredto divide the image into a plurality of image portions arranged in amatrix, for determining whether there is an object in the backgroundimage that is not a marker. FIG. 6 illustrates an example of an image600 that is divided into different image portions 602 (or pixel blocks).Each image portion 602 has a size that may or may not be smaller than ablock spacing 604, but the image portions 602 should collectively covermost of the image 600 (e.g., they should be spread throughout the image600). In some embodiments, each image portion 602 has a width (e.g.,along an x-axis) that is the same as a height (e.g., a y-axis). In otherembodiments, each image portion 602 has a width that is different fromits height.

The size for one or more of the image portions 602 may be set manually.Alternatively, the processing unit 206 may be configured to set the sizeof the image portions 602 automatically using an algorithm. In oneimplementation, the processing unit 206 may employ an algorithm forautomatically set the size of the image portions 602. The processingunit 206 may take an initial image frame and determine a “local”standard deviation of pixel values, e.g., a standard deviation over asmall region. This will provide a measure of the statistical noise inthe image. In some embodiments, such may be accomplished by measuringthe standard deviation of pixel values over a block (e.g., 5×5 size),and computing μ_(σ), the average of all such standard deviations overall such blocks over the image. Such technique may allow the processingunit 206 to determine the variation due to noise but ignoring theeffects of large scale variations in grayscale value. In someembodiments, the processing unit 206 may be configured to determine thestandard deviation of the entire image. During a detection phase, theprocessing unit 206 may define a set of block sizes N1, N2, . . . Nn,where n is 2 or 3. The processing unit 206 performs the previouslydescribed basic detection algorithm on each image frame n times, usingeach of the block sizes in the set. For a given block size Ni, thestandard deviation of block averages may be the same as the standarderror of the mean (SEM) of grayscale values: SEM=μ_(σ)/Ni. Then thethreshold T for that block size should be set to some multiple of theSEM (e.g., T=3×SEM+offset), with the rationale that it should bestatistically unlikely for a value in the block value map to differ bymore than T from the average value in the map. Therefore, one mayconclude that such a block value is not due to noise. The smallest blocksize may be set as default to be 2 or 3 pixels in size, and the largestmay be set so that the SEM value is small (e.g., 0.3). In otherembodiments, the processing unit 206 may compute a standard deviationover the whole image (instead of over a portion of the image).

After the image portions 602 are determined, the processing unit 206then determines a mean or median value of pixel values in each of theimage portions 602 in the image. The image may be the entire imageframe, or a subset or a portion within the image frame. Next, theprocessing unit 206 determines a histogram using the determined mean ormedian values. The processing unit 206 then determines if any of themean or median values exceeds a peak value of the histogram by more thana specified threshold. If so, then the processing unit 206 may determinethat there is an object in the background that is not a marker.

Returning to FIG. 5, if the processing unit 206 determines that there isan object in the background that is not a marker, the processing unit206 then excludes the object as a marker for future processing in aprocedure and/or stops the procedure (item 506). For example, in someembodiments, the procedure may be a tracking of a tissue, treatment of atissue, or a gating of a medical process (e.g., gating a delivery of aradiation or proton beam). In such cases, when the presence of theobject has been identified in the background image, the processing unit206 may generate a signal to stop the procedure, and then removes theobject from the camera image so that the object is excluded as a markerin the procedure. After the object has been excluded as a marker, theprocessing unit 206 may generate another signal to re-start theprocedure. Alternatively, the procedure may remain stopped unit an input(e.g., an instruction to re-start the procedure) is received from auser. In some embodiments, the procedure is stopped until a decisionbased on tracking is made (e.g., by the processing unit 206, by anotherprocessing unit, or by a user). For example, the decision may be whetherto continue with treatment, whether to operate a component of atreatment system, such as whether to rotate a radiation source, to movea patient support, to operate a collimator, etc, or other decisionsrelated to a medical procedure.

In some embodiments, if none of the mean or median values exceeds thepeak value of the histogram by more than the specified threshold, thenprocessing unit 206 may determine that there is no “non-marker” objectin the background.

The method 500 is advantageous because it allows detection of pixels inthe image (other than the designated foreground pixels, such as pixelsof marker images) that are visibly brighter than the average background.Thus, all objects that are distinguishable from noise, and that are notthe markers intended to be detected, can be detected.

In some embodiments, the method 500 may optionally also includeflattening the image in greyscale so that gradient variation across theimage is reduced. This feature may be desirable because in some cameraimages, there may be a gradient in grayscale over the whole image whichmay tend to create false positives in the background object detection.In such cases, it may be beneficial to planarize the image (e.g.,flatten it in grayscale) so that the gradient variation is reduced, oras small as possible. In one implementation, the processing unit 206 isconfigured for sampling a set of points in the image. For example, theprocessing unit 206 may take a subsample set of points, such as an 3×3points grid 700, from the image 702 (FIG. 7). Each point may have avalue that is an average of a 3×3 set of pixels centered about the pointlocation. In other example, the grid 700 may be a 8×12 grid, with eachpoint being a value that is an average of a 3×3 set of pixels centeredabout the point location. The processing unit 206 then generates anuniform gradient image 704 with uniform grayscale gradient which is thebest-fit to the sampled set of points. One way to think of this is totreat the grayscale as a third dimension, and to represent the grid ofpoints as a 3D plot in which the grayscale value at each pointrepresents the “height” of the point at each x, y position. The uniformgradient image may be represented by a plane 704 which is the best fitto that 3D grid 700 (e.g., by least-square fitting, etc.). Theprocessing unit 206 then subtracts the uniform gradient image 704 fromthe received image 702 to generate an output image 706 (a more“planarized” image in terms of grayscale). The output image 706 may thenbe processed to identify a possible object in the background (in item504). In some embodiments, the output image 706 may be used as the imagein item 502. In such cases, item 502 may be performed by the processingunit 206 obtaining the output image 706 (e.g., by receiving the outputimage from another processing unit, or by determining the output image706 using the above described flattening procedure).

Also, in some embodiments, a user may specify a set of foregroundpixels, which are not to be treated as background, and are to beexcluded from detection. In such cases, the algorithm for implementingthe method 500 may handle this by setting the designated foregroundpixels to zero grayscale value.

In some embodiments, the method 500 may be performed by the processingunit 206 for every image frame received from the camera 204. Forexample, in some embodiments, the method 500 may be performed by theprocessing unit 206 fast enough so that it can be performed on everyimage frame from the camera video stream (e.g., with a 30 Hz frame rateor faster). In other embodiments, the method 500 may be performed by theprocessing unit 206 for every Nth image received from the camera 204.For example, in some embodiments, the processing unit 206 is configuredto receive a sequence of images from the camera 204, and is configuredto perform the method 500 on a subset of the sequence of images (e.g.,every 5th image).

In other embodiments, the processing unit 206 may be configured toselect only a portion of the image area as test block(s). The portionmay change from frame to frame to get total coverage over the course ofseveral frames. For example, an image frame may be divided into 4portions (4 quadrants). The processing unit 206 may process the firstquadrant for a first image, a second quadrant for a second image, athird quadrant for a third image, and a fourth quadrant for the fourthimage. In this way, every portion of the entire image area is examinedat least once for background objects over the course of several frames,but the processing unit 206 does not have to process every pixel of theimage on any one given frame.

In some embodiments, the determined position and/or orientation of themarker block 202 can then be used to position the patient 16 at desiredposition and/or orientation. For example, the determined position of themarker block 202 may be compared with a prescribed position of themarker block 202. In such cases, if the determined position of themarker block 202 matches with the prescribed position, the patient 16 isthen considered to be correctly positioned. On the other hand, if thedetermined position of the marker block 202 does not match theprescribed position, the patient 16 is then positioned (e.g., by movingthe patient support 14) until the marker block 202 position matches withthe prescribed position.

In other embodiments, the determined position and/or orientation of themarker block 202 can be used to determine the position of at least aportion of the patient 16. In such cases, the relative spatialrelationship between the marker block 202 and the patient 16 is known orpredetermined. As such, once the marker block 202 position isdetermined, the position of the portion of the patient 16 can then bedetermined (e.g., via the processing unit 206) based on the relativespatial relationship between the marker block 202 and the patient 16. Insome embodiments, by continuously determining the position of theportion of the patient 16 in real time, the portion of the patient 16can be tracked in real time. The tracked position of the patient 16 maybe used to gate an application of radiation provided by the system 10.In further embodiments, the tracked position of the patient 16 may beused to perform tracking of a target region while an intensity modulatedradiation therapy (IMRT) is being performed. In IMRT, a multi-leafcollimator is operated such that a first portion of the target regionreceives more radiation than a second portion of the target regionduring a treatment session.

In further embodiments, the determined position of the marker block 202can be used to determine a level of activity accomplished by the patient16. For example, if the marker block 202 is placed on the patient'schest, then the determined position of the marker block 202 can be usedto determine a level of breathing performed by the patient 16. In somecases, by determining a plurality of positions of the marker block 202over a period of time, the processing unit 206 can be configured toobtain a plurality of amplitude points that correspond to the patient'slevels of breathing at various time points in that period. Thedetermined amplitude points may be used to gate an execution of aprocedure, such as, to gate an application of a treatment radiation tothe patient 16 for treatment, or to gate an application of an imagingradiation to the patient 16 for imaging purpose. In other embodiments,the determined positions of the marker block 202 (or the amplitudepoints) may be used to gate a binning of image data, either in realtime, or after the image data has been obtained. In further embodiments,the amplitude points may be used to perform tracking of a target regionwhile IMRT is being performed. Since the amplitude values are determinedusing only the marker images without any object image from thebackground image, the gating of the medical procedure is based on onlythe marker images, and any object in the background image is excludedfor the act of gating.

In further embodiments, by determining a plurality of positions of themarker block 202 over a period of time, the processing unit 206 can beconfigured to obtain a plurality of phase points that correspond todifferent levels of completeness of a breathing cycle at various timepoints. For example, a phase value may have a value from 0° to 360°,with 0° representing a beginning of a respiratory cycle, and 360°representing an end of the respiratory cycle. FIG. 8 illustrates anexample of a phase diagram 800 that is aligned with a correspondingamplitude/position diagram 802. Amplitude diagram 802 includespositional points of the marker block 202 determined using embodimentsof the technique described herein. Each point in the amplitude diagram802 represents a position of the marker block 202 or a bodily part at acertain point in time. In the illustrated example, a phase value of 0°(and 360°) represents a peak of an inhale state, and the phase valuevaries linearly between 0° and 360° in a physiological cycle. As shownin the diagram, for each point in the amplitude diagram 802 at certainpoint in time, a corresponding phase value at the same point in time maybe obtained. Thus, for each breathing amplitude, the processing unit 206can determine the corresponding phase of the respiratory cycle.

In some embodiments, the determined phase values may be used to gate anexecution of a procedure, such as, to gate an application of a treatmentradiation to the patient 16 for treatment, or to gate an application ofan imaging radiation to the patient 16 for imaging purpose. In furtherembodiments, the phase values may be used to perform tracking of atarget region while IMRT is being performed. Since the phase values aredetermined using only the marker images without any object image fromthe background image, the gating of the medical procedure is based ononly the marker images, and any object in the background image isexcluded for the act of gating.

In other embodiments, the determined phase values may be used to gate abinning of image data, either in real time while the image data is beingobtained, or after the image data has been obtained. For example, in a4D-CT imaging session, the marker system 200 may be used to determinethe positions of the marker block 202 representing different breathingamplitudes of the patient 16, while a CT machine generates differentprojection images of the patient 16 at different respective gantryangles. The positions of the marker block 202 may be used to determinebreathing phases for association with different projection images. Forexample, different projection images generated at different gantryangles but belonging to a same phase range (phase bin) may be associatedtogether. The associated projection images may then be used to constructa volumetric CT image for that particular phase bin. Also, in someembodiments, different volumetric CT images for different phase bins maybe constructed (e.g., using the processing unit 206 or anotherprocessor), and the sequence of volumetric CT images may be displayed ina video.

One advantage to using the marker block 202 is that with a-prioriknowledge of the relative positions of the markers 208 on the markerblock 202, it is possible to determine all six degrees of freedom (X, Y,Z, θ_(x), θ_(y), θ_(z)) of the marker block 202 from a single cameraview. In other words, only a single camera is required to derive theabsolute coordinates of a marker block 202. This results because therelative positioning between the markers 208 on the marker block 202 areknown, and the absolute coordinates and viewing orientation of thecamera 204 are also known. The detected image of the marker block 202 bythe camera 204 indicates the positioning of the visible referencelocations 208 relative to the camera's viewing orientation. Because theactual relative positions between the markers 208 are known, thedetected relative coordinates of the markers 208 from the camera imagecan be used to derive the absolute coordinate of the marker block 202.The marker block 202 is also advantageous because its configurationallows the camera 204 to detect the markers 208 accurately.

Although the marker system 200 has been described as having one camera204, in other embodiments, the marker system 200 can have more than onecamera. For example, in alternative embodiments, the marker system 200may include two cameras which detect the markers 208. In such cases, theprocessor 54/206 receives image data from the two cameras, anddetermines a position of the marker block 202 using triangulationtechnique, as is known in the art. Also, in other embodiments, insteadof a camera, the marker system 200 may include other types of opticaldevices that are capable of detecting the markers 208.

Also, it should be understood by those skilled in the art that themarker system 200 can be used with different systems in differentembodiments. For example, the radiation system 10 needs not be atreatment device, and may be any machine that is capable of generating aradiation beam. In some embodiments, the radiation system 10 may be anytypes of imaging or optical devices, such as a CT imaging device (e.g.,a cone beam CT device), a laminar tomography machine, a MRI machine, aC-arm based x-ray imaging machine, a three dimensional angiographymachine, or a PET machine. Also, in other embodiments, any of the markersystems 200 and/or methods described herein can be used with non-imagingdevices, such as a positioner or a treatment machine that has no imagingcapability. In further embodiments, any of the marker systems 200 and/ormethods described herein can be used with a machine that has a pluralityof radiation sources. For example, the machine can have a firstradiation source for delivering diagnostic radiation (e.g., radiationhaving an energy level in the kilo-electron-volt range), and a secondradiation source for delivering treatment radiation (e.g., radiationhaving an energy level in the mega-electron-volt range). As anotherexample, the machine can also have a plurality of diagnostic radiationsources and/or one or more treatment radiation sources.

Also, in other embodiments, instead of using markers that emit light andcamera that detects light, other types of energy/signal emitting devicesand signal detectors may be used. For example, in other embodiments,electromagnetic field beacons may be used as markers that emitelectromagnetic signals. In one implementation, Calypso beaconsavailable from Varian Medical Systems, Inc. may be placed on a markerblock. The beacons provide electromagnetic emission and the positions ofthe beacons may be detected by an electromagnetic detector array that isexterior to the patient. In some embodiments, the beacons may be excitedby an external source. In further embodiments, instead of light orelectromagnetic signal, the markers may emit other types of signal.

Computer System Architecture

FIG. 9 is a block diagram illustrating an embodiment of a computersystem 1600 that can be used to implement various embodiments describedherein. Computer system 1600 includes a bus 1602 or other communicationmechanism for communicating information, and a processor 1604 coupledwith the bus 1602 for processing information. The processor 1604 may bean example of the processor 54 of FIG. 1, an example of the processingunit 206 of FIG. 2, or an example of any processor described herein. Thecomputer system 1600 also includes a main memory 1606, such as a randomaccess memory (RAM) or other dynamic storage device, coupled to the bus1602 for storing information and instructions to be executed by theprocessor 1604. The main memory 1606 also may be used for storingtemporary variables or other intermediate information during executionof instructions to be executed by the processor 1604. The computersystem 1600 further includes a read only memory (ROM) 1608 or otherstatic storage device coupled to the bus 1602 for storing staticinformation and instructions for the processor 1604. A data storagedevice 1610, such as a magnetic disk or optical disk, is provided andcoupled to the bus 1602 for storing information and instructions.

The computer system 1600 may be coupled via the bus 1602 to a display167, such as a cathode ray tube (CRT), for displaying information to auser. An input device 1614, including alphanumeric and other keys, iscoupled to the bus 1602 for communicating information and commandselections to processor 1604. Another type of user input device iscursor control 1616, such as a mouse, a trackball, or cursor directionkeys for communicating direction information and command selections toprocessor 1604 and for controlling cursor movement on display 167. Thisinput device typically has two degrees of freedom in two axes, a firstaxis (e.g., x) and a second axis (e.g., y), that allows the device tospecify positions in a plane.

In some embodiments, the computer system 1600 can be used to performvarious functions described herein. According to some embodiments, suchuse is provided by computer system 1600 in response to processor 1604executing one or more sequences of one or more instructions contained inthe main memory 1606. Those skilled in the art will know how to preparesuch instructions based on the functions and methods described herein.Such instructions may be read into the main memory 1606 from anothercomputer-readable medium, such as storage device 1610. Execution of thesequences of instructions contained in the main memory 1606 causes theprocessor 1604 to perform the process steps described herein. One ormore processors in a multi-processing arrangement may also be employedto execute the sequences of instructions contained in the main memory1606. In alternative embodiments, hard-wired circuitry may be used inplace of or in combination with software instructions to implement thevarious embodiments described herein. Thus, embodiments are not limitedto any specific combination of hardware circuitry and software.

The term “computer-readable medium” as used herein refers to any mediumthat participates in providing instructions to the processor 1604 forexecution. Such a medium may take many forms, including but not limitedto, non-volatile media, volatile media, and transmission media.Non-volatile media includes, for example, optical or magnetic disks,such as the storage device 1610. Volatile media includes dynamic memory,such as the main memory 1606. Transmission media includes coaxialcables, copper wire and fiber optics, including the wires that comprisethe bus 1602. Transmission media can also take the form of acoustic orlight waves, such as those generated during radio wave and infrared datacommunications.

Common forms of computer-readable media include, for example, a floppydisk, a flexible disk, hard disk, magnetic tape, or any other magneticmedium, a CD-ROM, any other optical medium, punch cards, paper tape, anyother physical medium with patterns of holes, a RAM, a PROM, and EPROM,a FLASH-EPROM, any other memory chip or cartridge, a carrier wave asdescribed hereinafter, or any other medium from which a computer canread.

Various forms of computer-readable media may be involved in carrying oneor more sequences of one or more instructions to the processor 1604 forexecution. For example, the instructions may initially be carried on amagnetic disk of a remote computer. The remote computer can load theinstructions into its dynamic memory and send the instructions over atelephone line using a modem. A modem local to the computer system 1600can receive the data on the telephone line and use an infraredtransmitter to convert the data to an infrared signal. An infrareddetector coupled to the bus 1602 can receive the data carried in theinfrared signal and place the data on the bus 1602. The bus 1602 carriesthe data to the main memory 1606, from which the processor 1604retrieves and executes the instructions. The instructions received bythe main memory 1606 may optionally be stored on the storage device 1610either before or after execution by the processor 1604.

The computer system 1600 also includes a communication interface 1618coupled to the bus 1602. The communication interface 1618 provides atwo-way data communication coupling to a network link 1620 that isconnected to a local network 1622. For example, the communicationinterface 1618 may be an integrated services digital network (ISDN) cardor a modem to provide a data communication connection to a correspondingtype of telephone line. As another example, the communication interface1618 may be a local area network (LAN) card to provide a datacommunication connection to a compatible LAN. Wireless links may also beimplemented. In any such implementation, the communication interface1618 sends and receives electrical, electromagnetic or optical signalsthat carry data streams representing various types of information.

The network link 1620 typically provides data communication through oneor more networks to other devices. For example, the network link 1620may provide a connection through local network 1622 to a host computer1624 or to equipment 1626 such as a radiation beam source or a switchoperatively coupled to a radiation beam source. The data streamstransported over the network link 1620 can comprise electrical,electromagnetic or optical signals. The signals through the variousnetworks and the signals on the network link 1620 and through thecommunication interface 1618, which carry data to and from the computersystem 1600, are exemplary forms of carrier waves transporting theinformation. The computer system 1600 can send messages and receivedata, including program code, through the network(s), the network link1620, and the communication interface 1618.

It should be noted that as used in this specification, the term “image”may refer to an image that is displayed (e.g., in a screen), or an imagethat is stored in a non-transitory medium.

Although particular features have been shown and described, it will beunderstood that they are not intended to limit the claimed invention,and it will be made obvious to those skilled in the art that variouschanges and modifications may be made without departing from the spiritand scope of the claimed invention. The specification and drawings are,accordingly to be regarded in an illustrative rather than restrictivesense. The claimed invention is intended to cover all alternatives,modifications and equivalents.

1. An image processing method, comprising: obtaining an image, the imagehaving marker images and a background image; identifying presence of anobject in the background image using a processor; and providing a signalfor stopping a procedure if the presence of the object is identified. 2.The method of claim 1, wherein the act of identifying the presence ofthe object in the background comprises: dividing the image into aplurality of image portions arranged in a matrix; and determines a meanor median value of pixel values in each of the image portions.
 3. Themethod of claim 2, wherein the act of identifying the presence of theobject in the background further comprises determining a histogram usingthe determined mean or median values.
 4. The method of claim 3, whereinthe act of identifying the presence of the object further comprisesdetermining if any of the mean or median values exceeds a peak value ofthe histogram by more than a specified threshold.
 5. The method of claim2, further comprising setting a size for one or more of the imageportions.
 6. The method of claim 5, wherein the size is set manually. 7.The method of claim 5, wherein the size is set automatically using theprocessor.
 8. The method of claim 1, further comprising flattening theimage in greyscale so that gradient variation across the image isreduced.
 9. The method of claim 8, wherein the act of flattening theimage in greyscale comprises: sampling a set of points in the image;generating an uniform gradient image with uniform grayscale gradientwhich is the best-fit to the sampled set of points; and subtracting theuniform gradient image from the received image to generate an outputimage.
 10. The method of claim 1, further comprising excluding theobject as a marker.
 11. The method of claim 1, wherein the act ofreceiving an image comprises receiving a sequence of images thatincludes the image, and the act of identifying the presence of theobject is performed on a subset of the sequence of images.
 12. An imageprocessing apparatus, comprising: a processor configured for: obtainingan image, the image having marker images and a background image;identifying presence of an object in the background image; and providinga signal for stopping a procedure if the presence of the object isidentified.
 13. The apparatus of claim 12, wherein the processor isconfigured for: dividing the image into a plurality of image portionsarranged in a matrix; and determines a mean or median value of pixelvalues in each of the image portions.
 14. The apparatus of claim 13,wherein the processor is configured for determining a histogram usingthe determined mean or median values.
 15. The apparatus of claim 14,wherein the processor is configured for determining if any of the meanor median values exceeds a peak value of the histogram by more than aspecified threshold.
 16. The apparatus of claim 13, wherein theprocessor is configured to obtain a size for one or more of the imageportions.
 17. The apparatus of claim 16, wherein the processor isconfigured to obtain the size by receiving an input from a user thatrepresents the size.
 18. The apparatus of claim 16, wherein theprocessor is configured to obtain the size by determining the size usingan algorithm.
 19. The apparatus of claim 12, wherein the processor isfurther configured for flattening the image in greyscale so thatgradient variation across the image is reduced.
 20. The apparatus ofclaim 19, wherein the processor is configured to perform the act offlattening the image in greyscale by: sampling a set of points in theimage; generating an uniform gradient image with uniform grayscalegradient which is the best-fit to the sampled set of points; andsubtracting the uniform gradient image from the received image togenerate an output image.
 21. The apparatus of claim 12, wherein theprocessor is further configured to exclude the object as a marker. 22.The apparatus of claim 12, wherein the processor is configured toreceive a sequence of images that includes the image, and the processoris configured to perform the act of identifying the presence of theobject on a subset of the sequence of images.
 23. A computer producthaving a non-transitory medium storing a set of instructions, anexecution of which causes an image processing method to be performed,the method comprising: receiving an image, the image having markerimages and a background image; identifying presence of an object in thebackground image; and providing a signal for stopping a procedure if thepresence of the object is identified.